A low noise biopotential amplifier intended for Cochlear Implant using FINFET 22nm technology

A low noise biopotential amplifier intended for Cochlear Implant using FINFET 22nm technology | Research Square window.SnipcartSettings = { analytics: { enabled: false } }; (function() { var accessVector = localStorage.getItem('access_vector') || ''; window.dataLayer = window.dataLayer || []; if (accessVector) { window.dataLayer.push({ user: { profile: { profileInfo: { snid: accessVector } } } }); } })(); (function(w,d,s,l,i){w[l]=w[l]||[];w[l].push({'gtm.start':new Date().getTime(),event:'gtm.js'});var f=d.getElementsByTagName(s)[0],j=d.createElement(s),dl=l!='dataLayer'?'&l='+l:'';j.async=true;j.src='https://www.googletagmanager.com/gtm.js?id='+i+dl;f.parentNode.insertBefore(j,f);})(window,document,'script','dataLayer','GTM-K279D39R'); Browse Preprints In Review Journals COVID-19 Preprints AJE Video Bytes Research Tools Research Promotion AJE Professional Editing AJE Rubriq About Preprint Platform In Review Editorial Policies Our Team Advisory Board Help Center Sign In Submit a Preprint Cite Share Download PDF Research Article A low noise biopotential amplifier intended for Cochlear Implant using FINFET 22nm technology Hima Bindu Katikala, Sadulla Shaik This is a preprint; it has not been peer reviewed by a journal. https://doi.org/ 10.21203/rs.3.rs-3412444/v1 This work is licensed under a CC BY 4.0 License Status: Posted Version 1 posted You are reading this latest preprint version Abstract Electrical stimulus inside the ear to provide an auditory response using advanced prosthesis for the deaf people is a challenging task. Recent advance like cochlear implant prosthesis with in-built electrode array configuration converts the acoustic energy to the electrical stimulus. In this article, we discuss about the invention of different hearing aid designed for hearing impairment patient. A biopotential amplifier is utilised in the internal unit of a cochlear implant to reduce noise from the external unit and radio frequency components. It is designed using the advanced Fin Field Effect Transistor (FINFET) 22 nm technology and compare the results with conventional CMOS technology. The operating voltage applied to entire design is of 0.45v, the measured noise is of 133.0563 nv/√Hz at 50Hz frequency. Cochlear Implant (CI) Fin Field Effect Transistor (FINFET) Prosthesis Biopotential Amplifier Noise Analysis Figures Figure 1 Figure 2 Figure 3 Figure 4 Figure 5 Figure 6 Figure 7 Figure 8 Figure 9 Figure 10 Figure 11 Figure 12 Figure 13 1. INTRODUCTION The human ear system served as a sound transducer and is referred to as the organ of hearing and balance. It utilises the transduction mechanism, which transforms sound waves into electrochemical impulses, to detect and evaluate sound. If the anatomy is off, auditioning cannot be done properly. Many advanced prosthesis are available in order to prosthesis the human auditory nerves with external stimulus. Upon all the cochlear implant (CI) with the wireless power transfer functionality is reliable and compactable prosthesis [1]. In CI, the transmission of acoustic signals is through the transduction vibration mechanism [2-3]. Vibration mechanism functionality differs from the sound conduction mechanism: compile with the sound in inner and outer most ear. As in Fig.1, progression of acoustic energy in the ear initial begins at ear canal by pinna, when sound waves strike the eardrum transduces it mechanical energy. Mechanical energy initiates the ossicles (3 parts- stapes, incus & malleus) into fluid motion when strikes the oval window of cochlea and further the fluid movement in cochlea activates the delicate hair cells that create an electrical signal via auditory nerve, henceforth the sound is elucidate [4-5]. Normal hearing range of humans is of 20-20000 Hz lies in -10 to 25dB will diverge based on the hearing loss in-patient. In common, there are three kinds of hearing losses i.e. conductive, sensorineural & mixed hearing loss will be examined by standard Audiometric test, Weber test through Air/Bone conduction methodology and auditory brainstem response (ABR) [6]. ABR test mainly evaluate the tinnitus, includes electrode insertion on the scalp of skull to record the electrical activity of brain (EEG) as in Fig.2. When the acoustic wave’s passes through the ear will activate brain stem and central auditory nerve , give the response of tinnitus based on 10 adolescent with standard ABR parameters like amplitude and latencies [7]. 2. DIFFERENT KINDS OF HEARING AIDS PROSTHESIS Many existing hearing prosthesis are available to regularities the functionality of damage ear into normal condition. The purest tone of the sound sensing test in ear is done by audiogram describes the hearing loss type degree and configuration. Fig.3 illustrate the frequency vs hearing levels (in dB) for both the left and right ear, the mild and moderate hearing loss causes the conduction and sensorineural loss, whereas the severe & profound leads to mixed hearing loss [8]. 2.1. Programmable hearing aid prosthesis A programmable hearing aid (PHA) prosthesis as in Fig.4 has the pre-processing unit that includes the preamplifier with noise reduction filters attenuates at particular user defined frequency range [9]. In PHA, the frequency dependent amplifier principle is adapted and the signal processing characterized as per spectrum parameters from microphone to desired filter, further programmed by computer interface based on patient possibilities. 2.2. Normal hearing aid (NHA) prosthesis The NHA prosthesis designed for the patients of mild hearing loss (as in Fig.3) provided with the selective amplification, having the feature of Anti-Larsen that prevent the anti-oscillation of loudspeaker as shown in Fig.5. At the input stage, an Anti-wind microphone is preferred to trim down the whistling consequences [10]. 2.3. Bone-integrated hearing aid (BHA) prosthesis BHA directly transmits the sound to the inner ear is a simple prosthesis approved by FDA for adults in 1996 & for children’s above 5 years in 1999. BHA design modality begins with signal acquisition from microphone further given to amplifier for enhanced amplification [11]. Radio frequency telemetry data transmission carried through inductive coil with the principle of mutual inductance, both the transmitter (microphone & amplifier) 2.4. Numerical hearing aid (NUHA) prosthesis NUHA prosthesis functionality is based on electrical stimulus that generates impulse to auditory nerve. In NUHA, digital filters are used to split the acoustic signal to a high or low frequency compression through a gain controller [12]. All the digital filters are processed independently with separate edge. As NHUA is digitally proessed, henceforth their exist less distortion. 2.5. Cochlear Implant Primary goal of cochlear implant (CI) is to provide the electrical stimulus to restore the hearing in deaf patients. Fig.8 represents the pictorial representation of the CI system functionality that converts sound to electrical impulses. Digital signal processing (DSP) unit, a power amplifier, and a transmitter RF-link are all components of a modern CI's external speech processor unit [13]. The DSP processor converters the sound signal into bit streams and transmits the data through RF-link. DSP also have the memory allocation unit called ‘maps’ stores the patient information. In internal unit, the RF receiver sends data to simulator, simulator driven by the RF power (as of battery free device) and the data is decoded into the electrical current signals by stimulator as in Fig.9. 3. FINFET trends in COCHLEAR IMPLANT A multi-gate device known as a fin field-effect transistor (FinFET) is constructed on a substrate with gates attached to two, three, or four sides of the channel, creating a double gate configuration. [14]. Benefits include higher switching speeds, higher output current per input voltage, and reduced power consumption due to lower equivalent input capacitance. Due to the source and drain areas being physically separated more effectively, channel quantization effects also lessen short-channel effects. The electronics in CI's scope are designing functioning circuits like speech processors transmitter, etc. using VLSI technology. Signal processing from the external source to the ear's internal part is perfectly prototyped in Fig.9. An ASIC chip with a power amplifier, and an error-free decoder/demodulator [15] and Analog to Digital Converter (ADC) is integrated for internal feedback purposes. However, propagating the signal impulse in the millivolt (mv) range into the body is crucial. The array of 22 active platinum electrodes in CI has a length of 17 millimetres, each electrode has an isolation of 0.1 millimetres, and it facilitates the biphasic electric stimulus to the auditory nerve [16] and spiral ganglion nerve as in Fig.10 3.1. Design of RF biopotential amplifier (Internal unit amplifier) for CI using FINFET technology. A current-mode biopotential amplifier (INA) is employed for improved maximization because it eliminates DC offset and noise rates by giving maximum open-loop gain and a Common Mode Rejection Ratio (CMRR) with higher precision and reliability [17–18]. A differential amplifier (A3) is preferred due to its unique gain resistance. Biopotential amplifier is primarily made up of three op-amps that serve as buffers (A1 & A2). The voltage loss across its gain resistor (Rg), which subsequently decides its closed-loop gain of the INA thus possibly lowers the resistance incompatibility impedance with a reference voltage, is caused by negative feedback (inverting feedback of both op-amps) (Vr). The recommended amplifier designed to function at a low-frequency range with a greater CMRR and survive at low voltage operations. The resulted signal is subjected to an RC low pass filter, which eliminates the high-frequency elements as in Fig.11. Built to work underneath the cut-off frequency, the recorded output voltage (Va) is 994.16 mv. A potential divider is utilized to lower the voltage level off a sensor to necessary value; the output voltage level is represented in Eq. (3). The measured noise levels are lower than the typical INA-DAC noise, with peak levels at 181 nv/√Hz (at 1 Hz) and minimum levels at 133.0563 nv/√Hz (at 50 Hz), as shown in Fig.12 (a) & (b). 3.2. Calculation for Bit Error Rate (BER) at RF receiver: BER is defined as the difference in bits between the transmitted inputs (IN) 12K bits to the received output bits with an error of 4 bits (VOUT). Since error bits are calculated as four divided by the 12K transmitted bits, the error rate is 0.0000333. Change in data transmission is caused because of the channel loss, cosmic noise, and internal noise Conclusion The various hearing aid advancements are covered in this work, and an RF biopotential amplifier is constructed for use with cochlear implants using 20nm FINFET technology. For coherent noise, reduction at receiver side the biopotential amplifier is configured in the internal unit of cochlear implant. For Conventional design methodology, a RC low pass filter is integrated to suppress the high frequency components present and the potential divider at output stage lower the voltage swing to greater extent of required microvolts of biomedical signal. Noise analysis of biopotential amplifier is measured at low & high frequency range. With this cutting-edge FINFET technology, the performance of the cochlear implant is now increased by 30% in terms of latency reduction to 34.38% and power dissipation to 1.54% compared to standard approach in CMOS. Declarations Compliance with Ethical Standards The authors have no relevant financial or non-financial interests to disclose. The authors have no conflicts of interest to declare relevant to this article’s content. All authors certify that they have no affiliations with or involvement in any organization or entity with any financial or non-financial interest in the subject matter or materials discussed in this manuscript. The authors have no financial or proprietary interests in any material discussed in this article. The research not involving any human participants and/or animals. References Al-Haddad K,"A modified wireless power transfer system for medical implants", Energies , 2019, 12(10), 1-21, DOI https://doi.org/10.3390/en12101890 Haumann S, Bauernfeind G, Teschner MJ, Schierholz I, Bleichner MG, Büchner A, Lenarz T, "Epidural recordings in cochlear implant users", Journal of neural engineering , 2019, 16(5), DOI https://doi.org/10.1088/1741-2552/ab1e80 Zeng FG, Rebscher S, Harrison W, Sun X, Feng H, "Cochlear implants: system design, integration, and evaluation", IEEE reviews in biomedical engineering, 2008, 1, 115-42, DOI 10.1109/RBME.2008.2008250 Heine, P. A, “Anatomy of the ear”,Veterinary Clinics: Small Animal Practice, 2004, 34(2), 379-395. Luers, Jan Christoffer, Karl‐Bernd Hüttenbrink, "Surgical anatomy and pathology of the middle ear" Journal of anatomy, 2016, 228(2), 338-353. Skoe, Erika, Nina Kraus, "Auditory brainstem response to complex sounds: a tutorial." Ear and hearing, 2010, 31(3), 302. Han, M. S., Jeong, Y. J., Im, G. J., Song, J. J., Chae, S. W., Rah, Y. C., Choi, J, “Auditory brainstem response test results in normal hearing adolescents with subjective tinnitus”, International Journal of Pediatric Otorhinolaryngology, 2021, 146, 110775. Courtois, G., Grimaldi, V., Lissek, H., Estoppey, P., Georganti, E, “Perception of auditory distance in normal-hearing and moderate-to-profound hearing-impaired listeners.” Trends in hearing, 2019, 23, 2331216519887615. Lahiani, M., Amor, N. B., Ghariani, H., Hamida, A. B, “Adjustable filtering structure design dedicated to a programmable hearing aid apparatus”, International Journal of Physical Sciences, 2006, 1(4), 201-211. Most, T., Aviner, C, “Auditory, visual, and auditory–visual perception of emotions by individuals with cochlear implants, hearing aids, and normal hearing”. Journal of Deaf Studies and Deaf Education, 2009, 14(4), 449-464. Bento, R. F., Kiesewetter, A., Ikari, L. S., Brito, R, “Bone-anchored hearing aid (BAHA): indications, functional results, and comparison with reconstructive surgery of the ear”, International archives of otorhinolaryngology, 2012, 16(03), 400-405. Sanders, M. E., Kant, E., Smit, A. L., Stegeman, I, “The effect of hearing aids on cognitive function: A systematic review”, Plos one, 2021, 16(12), e0261207. H. Uluşan, S. Chamanian, B. İlik, A. Muhtaroğlu and H. Külah, "Fully Implantable Cochlear Implant Interface Electronics With 51.2µW Front-End Circuit," in IEEE Transactions on Very Large Scale Integration (VLSI) Systems , 2019, 27(7), 1504-1512, DOI 10.1109/TVLSI.2019.2898873 R. S. Pal, S. Sharma and S. Dasgupta, "Recent trend of FinFET devices and its challenges: A review", Conference on Emerging Devices and Smart Systems (ICEDSS) , 2017, 150-154. DOI: 10.1109/ICEDSS.2017.8073675 Gu Y, Aissa S, "RF-based energy harvesting in decode-and-forward relaying systems: Ergodic and outage capacities", IEEE Transactions on Wireless Communication , 2015, 14(11), 6425-434, DOI 10.1109/TWC.2015.2453418 Hussong A, Rau TS, Ortmaier T, Heimann B, Lenarz T, Majdani O, "An automated insertion tool for cochlear implants: another step towards atraumatic cochlear implant surgery", International journal of computer assisted radiology and surgery , 2010, 5(2), 163-171, DOI 10.1007/s11548-009-0368-0 Nagulapalli, R., Hayatleh, K., Barker, S., Zourob, S., Yassine, N., Raparthy, S., & Tammam, A. A novel high CMRR trans-impedance instrumentation amplifier for biomedical applications. Analog Integrated Circuits and Signal Processing,2019;98(2):233-241. DOI: https://doi.org/10.1007/s10470-018-1256-8 Srivastava, N., Shadab, A., & Shukla.G. Yokto (10-24V) Instrumentation Amplifier. IEEE Third International Conference on Computer and Communication Technology,2012;116-121. DOI: 10.1109/ICCCT.2012.31 Cite Share Download PDF Status: Posted Version 1 posted You are reading this latest preprint version Research Square lets you share your work early, gain feedback from the community, and start making changes to your manuscript prior to peer review in a journal. As a division of Research Square Company, we’re committed to making research communication faster, fairer, and more useful. We do this by developing innovative software and high quality services for the global research community. Our growing team is made up of researchers and industry professionals working together to solve the most critical problems facing scientific publishing. Also discoverable on Platform About Our Team In Review Editorial Policies Advisory Board Help Center Resources Author Services Accessibility API Access RSS feed Manage Cookie Preferences © Research Square 2026 | ISSN 2693-5015 (online) Privacy Policy Terms of Service Do Not Sell My Personal Information {"props":{"pageProps":{"initialData":{"identity":"rs-3412444","acceptedTermsAndConditions":true,"allowDirectSubmit":true,"archivedVersions":[],"articleType":"Research Article","associatedPublications":[],"authors":[{"id":411337176,"identity":"47dddac9-f609-4ccb-8d06-7d8ea1f67aee","order_by":0,"name":"Hima Bindu Katikala","email":"","orcid":"","institution":"Vignan's Foundation for Science Technology and Research","correspondingAuthor":false,"prefix":"","firstName":"Hima","middleName":"Bindu","lastName":"Katikala","suffix":""},{"id":411337177,"identity":"2826005d-1ea7-4d68-8f84-1c6b62baf99e","order_by":1,"name":"Sadulla Shaik","email":"data:image/png;base64,iVBORw0KGgoAAAANSUhEUgAAAZAAAAAyAQMAAABI0h/eAAAABlBMVEX///8AAABVwtN+AAAACXBIWXMAAA7EAAAOxAGVKw4bAAAA1klEQVRIiWNgGAWjYHACA4YHBQw8/OwNILYFkVoSDBjkJHsOgNgSxGsxNriRAOIQoUW+/fA2iQQDu8QNN59f3fCjQIKBv707Ab8VZ9LKgFqSE2fezim72QN0mMSZsxsIuCrHDKiFObHvdk7aDR6gFgOJXPxa5PvfgLTUJzbcPJN28w8xWhhugG05bCxwg/3YbaJsMbjxrNgiweA4MJBz2G7LGEjwEPSLfH/yxhsfKqqBUXn82c03f2zk+Nt7CTgMAXgMwCSxykGA/QEpqkfBKBgFo2AEAQCtwEg3NjJ8UwAAAABJRU5ErkJggg==","orcid":"https://orcid.org/0000-0003-3119-8905","institution":"KKR and KSR Institute of Technology and Sciences","correspondingAuthor":true,"prefix":"","firstName":"Sadulla","middleName":"","lastName":"Shaik","suffix":""}],"badges":[],"createdAt":"2023-10-05 07:46:03","currentVersionCode":1,"declarations":"","doi":"10.21203/rs.3.rs-3412444/v1","doiUrl":"https://doi.org/10.21203/rs.3.rs-3412444/v1","draftVersion":[],"editorialEvents":[],"editorialNote":"","failedWorkflow":false,"files":[{"id":75995328,"identity":"42a65996-3542-41d7-8475-86d6268a3b59","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":1,"title":"Figure 1","display":"","copyAsset":false,"role":"figure","size":270267,"visible":true,"origin":"","legend":"\u003cp\u003eAnatomy of Ear.\u003c/p\u003e","description":"","filename":"1.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/e0ae38d6764f0ce0039609bc.png"},{"id":75997077,"identity":"3d58d33c-8553-45bb-a3fc-719b069c07e9","added_by":"auto","created_at":"2025-02-11 09:58:01","extension":"png","order_by":2,"title":"Figure 2","display":"","copyAsset":false,"role":"figure","size":360708,"visible":true,"origin":"","legend":"\u003cp\u003e(A). Signal acquisition of auditory brainstem response (ABR). (B). ABR wave event latency with respect to amplitude\u003c/p\u003e","description":"","filename":"2.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/828ae9604e4203c92887d54f.png"},{"id":75997536,"identity":"50b6b17a-9eaa-456a-94b2-46b59dd0f4eb","added_by":"auto","created_at":"2025-02-11 10:06:01","extension":"png","order_by":3,"title":"Figure 3","display":"","copyAsset":false,"role":"figure","size":357452,"visible":true,"origin":"","legend":"\u003cp\u003eFrequency vs Hearing level (dB) of both left and right ear, differentiate the ranges of hearing loss.\u003c/p\u003e","description":"","filename":"3.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/b758fb6962ab3317159c3338.png"},{"id":75995332,"identity":"676c62c1-7a8e-4d06-9c28-895eca031bf2","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":4,"title":"Figure 4","display":"","copyAsset":false,"role":"figure","size":104355,"visible":true,"origin":"","legend":"\u003cp\u003eProgrammable hearing aid\u003c/p\u003e","description":"","filename":"4.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/a2bb0ab80bdc05b7deff5df1.png"},{"id":75995321,"identity":"0973cbef-0f8f-41ba-a79c-a67bbccb29b8","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":5,"title":"Figure 5","display":"","copyAsset":false,"role":"figure","size":113487,"visible":true,"origin":"","legend":"\u003cp\u003eNormal hearing aid (NHA) prosthesis\u003c/p\u003e","description":"","filename":"5.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/53ca1c2271d68550575f9cfa.png"},{"id":75995322,"identity":"01cc47f0-950b-4c7b-b7cb-b8bc722f5cd1","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":6,"title":"Figure 6","display":"","copyAsset":false,"role":"figure","size":63702,"visible":true,"origin":"","legend":"\u003cp\u003eBone-integrated hearing aid (BHA) prosthesis\u003c/p\u003e","description":"","filename":"6.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/08a28373ef6d02684fc13c31.png"},{"id":75995327,"identity":"62ea5bb3-670f-475f-9149-48330c5ca4dc","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":7,"title":"Figure 7","display":"","copyAsset":false,"role":"figure","size":91547,"visible":true,"origin":"","legend":"\u003cp\u003eNumerical hearing aid (NUHA) prosthesis\u003c/p\u003e","description":"","filename":"7.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/12d78d4a3d4ffafc807bf9b8.png"},{"id":75997080,"identity":"e413f0b3-4953-441a-8289-e9f704d5b7c9","added_by":"auto","created_at":"2025-02-11 09:58:01","extension":"png","order_by":8,"title":"Figure 8","display":"","copyAsset":false,"role":"figure","size":209255,"visible":true,"origin":"","legend":"\u003cp\u003eCochlea implant that converts sound to electrical impulses\u003c/p\u003e","description":"","filename":"8.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/91998b93872801107046cd57.png"},{"id":75995325,"identity":"c8dd4d99-7832-4628-a0c9-2137d585699b","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":9,"title":"Figure 9","display":"","copyAsset":false,"role":"figure","size":86329,"visible":true,"origin":"","legend":"\u003cp\u003eFunctional block diagram of CI.\u003c/p\u003e","description":"","filename":"9.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/2b2eb86728b238a0fc4ebb4e.png"},{"id":75995324,"identity":"edbc45bc-9790-4f64-9dfa-c804db09f233","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":10,"title":"Figure 10","display":"","copyAsset":false,"role":"figure","size":53146,"visible":true,"origin":"","legend":"\u003cp\u003eStructure of FINFET.\u003c/p\u003e","description":"","filename":"10.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/78460c097c14f8e8311dc925.png"},{"id":75997078,"identity":"28a3d06a-ea33-4131-a5ea-08cac68ad630","added_by":"auto","created_at":"2025-02-11 09:58:01","extension":"png","order_by":11,"title":"Figure 11","display":"","copyAsset":false,"role":"figure","size":102536,"visible":true,"origin":"","legend":"\u003cp\u003eFig.10 CI based Platinum Electrode Array\u003c/p\u003e","description":"","filename":"010.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/5fa88ba056bfe83c40745fcc.png"},{"id":75997537,"identity":"a38264d4-b697-45f0-b1d2-6ac08ab9f805","added_by":"auto","created_at":"2025-02-11 10:06:01","extension":"png","order_by":12,"title":"Figure 12","display":"","copyAsset":false,"role":"figure","size":167048,"visible":true,"origin":"","legend":"\u003cp\u003eFig.11. RF Biopotential amplifier at internal unit of CI.\u003c/p\u003e","description":"","filename":"11.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/62232ae23e00deec116c7c80.png"},{"id":75995333,"identity":"0063173a-fc05-4cac-aa9f-094b99d1da14","added_by":"auto","created_at":"2025-02-11 09:50:01","extension":"png","order_by":13,"title":"Figure 13","display":"","copyAsset":false,"role":"figure","size":375918,"visible":true,"origin":"","legend":"\u003cp\u003eFig.12 (a).Transient response of biopotential amplifier.\u003c/p\u003e\n\u003cp\u003eFig.12 (b).Noise analysis plot of amplifier at 1 \u0026amp; 50 Hz.\u003c/p\u003e","description":"","filename":"12.png","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/daeb859ca4d8f6c7171952c6.png"},{"id":78771606,"identity":"f3a4f256-0739-44f4-bf0e-2b4a7ab11be2","added_by":"auto","created_at":"2025-03-18 16:12:54","extension":"pdf","order_by":0,"title":"","display":"","copyAsset":false,"role":"manuscript-pdf","size":2816594,"visible":true,"origin":"","legend":"","description":"","filename":"manuscript.pdf","url":"https://assets-eu.researchsquare.com/files/rs-3412444/v1/bbfb9ddf-fb49-4514-bf5a-1bdd2cd1c3f9.pdf"}],"financialInterests":"","formattedTitle":"A low noise biopotential amplifier intended for Cochlear Implant using FINFET 22nm technology","fulltext":[{"header":"1.\tINTRODUCTION","content":"\u003cp\u003eThe human ear system served as a sound transducer and is \u0026nbsp;referred to as the organ of hearing and balance. It utilises the transduction mechanism, which transforms sound waves into electrochemical impulses, to detect and evaluate sound. If the anatomy is off, auditioning cannot be done properly. Many advanced prosthesis are available in order to prosthesis the human auditory nerves with external stimulus. Upon all the cochlear implant (CI) with the wireless power transfer functionality is reliable and compactable prosthesis [1]. In CI, the transmission of acoustic signals is through the transduction vibration mechanism [2-3]. Vibration mechanism functionality differs from the sound conduction mechanism: compile with the sound in inner and outer most ear. As in Fig.1, progression of acoustic energy in the ear initial begins at ear canal by pinna, when sound waves strike the eardrum transduces it mechanical energy. Mechanical energy initiates the ossicles (3 parts- stapes, incus \u0026amp; malleus) into fluid motion when strikes the oval window of cochlea and further the fluid movement in cochlea activates the delicate hair cells that create an electrical signal via auditory nerve, henceforth the sound is elucidate [4-5].\u0026nbsp;\u003c/p\u003e\n\u003cp\u003eNormal hearing range of humans is of 20-20000 Hz lies in -10 to 25dB will diverge based on the hearing loss in-patient. In common, there are three kinds of hearing losses i.e. conductive, sensorineural \u0026amp; mixed hearing loss will be examined by standard Audiometric test, Weber test through Air/Bone conduction methodology and auditory brainstem response (ABR) [6]. ABR test mainly evaluate the tinnitus, includes electrode insertion on the scalp of skull to record the electrical activity of brain (EEG) as in Fig.2. When the acoustic wave\u0026rsquo;s passes through the ear will activate brain stem and central auditory nerve , give the response of tinnitus based on 10 adolescent with standard ABR parameters like amplitude and latencies [7]. \u0026nbsp; \u0026nbsp; \u0026nbsp; \u0026nbsp; \u0026nbsp; \u0026nbsp; \u0026nbsp;\u003c/p\u003e"},{"header":"2.\tDIFFERENT KINDS OF HEARING AIDS PROSTHESIS","content":"\u003cp\u003eMany existing hearing prosthesis are available to regularities the functionality of damage ear into normal condition. The purest tone of the sound sensing test in ear is done by audiogram describes the hearing loss type degree and configuration. Fig.3 illustrate the frequency vs hearing levels (in dB) for both the left and right ear, the mild and moderate hearing loss causes the conduction and sensorineural loss, whereas the severe \u0026amp; profound leads to mixed hearing loss [8].\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e2.1. Programmable hearing aid prosthesis\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eA programmable hearing aid (PHA) prosthesis as in Fig.4 has the pre-processing unit that includes the preamplifier with noise reduction filters attenuates at particular user defined frequency range [9]. In PHA, the frequency dependent amplifier principle is adapted and the signal processing characterized as per spectrum parameters from microphone to desired filter, further programmed by computer interface based on patient possibilities.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e2.2. Normal hearing aid (NHA) prosthesis\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe NHA prosthesis designed for the patients of mild hearing loss (as in Fig.3) provided with the selective amplification, having the feature of Anti-Larsen that prevent the anti-oscillation of loudspeaker as shown in Fig.5. At the input stage, an Anti-wind microphone is preferred to trim down the whistling consequences [10].\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e2.3. Bone-integrated hearing aid (BHA) prosthesis\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eBHA directly transmits the sound to the inner ear is a simple prosthesis approved by FDA for adults in 1996 \u0026amp; for children\u0026rsquo;s above 5 years in 1999. BHA design modality begins with signal acquisition from microphone further given to amplifier for enhanced amplification [11]. Radio frequency telemetry data transmission carried through inductive coil with the principle of mutual inductance, both the transmitter (microphone \u0026amp; amplifier)\u0026nbsp;\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e2.4. Numerical hearing aid (NUHA) prosthesis\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eNUHA prosthesis functionality is based on electrical stimulus that generates impulse to auditory nerve. In NUHA, digital filters are used to split the acoustic signal to a high or low frequency compression through a gain controller [12]. All the digital filters are processed independently with separate edge. As NHUA is digitally proessed, henceforth their exist less distortion.\u0026nbsp;\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e2.5. Cochlear Implant\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003ePrimary goal of cochlear implant (CI) is to provide the electrical stimulus to restore the hearing in deaf patients. Fig.8 represents the pictorial representation of the CI system functionality that converts sound to electrical impulses. Digital signal processing (DSP) unit, a power amplifier, and a transmitter RF-link are all components of a modern CI\u0026apos;s external speech processor unit [13].\u0026nbsp;\u003c/p\u003e\n\u003cp\u003eThe DSP processor converters the sound signal into bit streams and transmits the data through RF-link. DSP also have the memory allocation unit called \u0026lsquo;maps\u0026rsquo; stores the patient information. In internal unit, the RF receiver sends data to simulator, simulator driven by the RF power (as of battery free device) and the data is decoded into the electrical current signals by stimulator as in Fig.9.\u0026nbsp;\u003c/p\u003e"},{"header":"3.\tFINFET trends in COCHLEAR IMPLANT","content":"\n\u003cp\u003eA multi-gate device known as a fin field-effect transistor (FinFET) is constructed on a substrate with gates attached to two, three, or four sides of the channel, creating a double gate configuration. [14]. Benefits include higher switching speeds, higher output current per input voltage, and reduced power consumption due to lower equivalent input capacitance. Due to the source and drain areas being physically separated more effectively, channel quantization effects also lessen short-channel effects.\u003c/p\u003e\n\u003cp\u003eThe electronics in CI's scope are designing functioning circuits like speech processors transmitter, etc. using VLSI technology. Signal processing from the external source to the ear's internal part is perfectly prototyped in Fig.9. An ASIC chip with a power amplifier, and an error-free decoder/demodulator [15] and Analog to Digital Converter (ADC) is integrated for internal feedback purposes. However, propagating the signal impulse in the millivolt (mv) range into the body is crucial. The array of 22 active platinum electrodes in CI has a length of 17 millimetres, each electrode has an isolation of 0.1 millimetres, and it facilitates the biphasic electric stimulus to the auditory nerve [16] and spiral ganglion nerve as in Fig.10\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e3.1. Design of RF biopotential amplifier (Internal unit amplifier) for CI using FINFET technology.\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eA current-mode biopotential amplifier (INA) is employed for improved maximization because it eliminates DC offset and noise rates by giving maximum open-loop gain and a Common Mode Rejection Ratio (CMRR) with higher precision and reliability [17–18]. A differential amplifier (A3) is preferred due to its unique gain resistance. Biopotential amplifier is primarily made up of three op-amps that serve as buffers (A1 \u0026amp; A2). The voltage loss across its gain resistor (Rg), which subsequently decides its closed-loop gain of the INA thus possibly lowers the resistance incompatibility impedance with a reference voltage, is caused by negative feedback (inverting feedback of both op-amps) (Vr). The recommended amplifier designed to function at a low-frequency range with a greater CMRR and survive at low voltage operations. The resulted signal is subjected to an RC low pass filter, which eliminates the high-frequency elements as in Fig.11. Built to work underneath the cut-off frequency, the recorded output voltage (Va) is 994.16 mv. A potential divider is utilized to lower the voltage level off a sensor to necessary value; the output voltage level is represented in Eq. (3). The measured noise levels are lower than the typical INA-DAC noise, with peak levels at 181 nv/√Hz (at 1 Hz) and minimum levels at 133.0563 nv/√Hz (at 50 Hz), as shown in Fig.12 (a) \u0026amp; (b).\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003e\u003cem\u003e3.2. Calculation for Bit Error Rate (BER) at RF receiver:\u003c/em\u003e\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eBER is defined as the difference in bits between the transmitted inputs (IN) 12K bits to the received output bits with an error of 4 bits (VOUT). Since error bits are calculated as four divided by the 12K transmitted bits, the error rate is 0.0000333. Change in data transmission is caused because of the channel loss, cosmic noise, and internal noise\u003c/p\u003e"},{"header":"Conclusion","content":"\u003cp\u003eThe various hearing aid advancements are covered in this work, and an RF biopotential amplifier is constructed for use with cochlear implants using 20nm FINFET technology. For coherent noise, reduction at receiver side the biopotential amplifier is configured in the internal unit of cochlear implant. For Conventional design methodology, a RC low pass filter is integrated to suppress the high frequency components present and the potential divider at output stage lower the voltage swing to greater extent of required microvolts of biomedical signal. Noise analysis of biopotential amplifier is measured at low \u0026amp; high frequency range. With this cutting-edge FINFET technology, the performance of the cochlear implant is now increased by 30% in terms of latency reduction to 34.38% and power dissipation to 1.54% compared to standard approach in CMOS.\u0026nbsp;\u003c/p\u003e"},{"header":"Declarations","content":"\u003cp\u003e\u003cstrong\u003eCompliance with Ethical Standards\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe authors have no relevant financial or non-financial interests to disclose.\u003c/p\u003e\n\u003cp\u003eThe authors have no conflicts of interest to declare relevant to this article’s content.\u003c/p\u003e\n\u003cp\u003eAll authors certify that they have no affiliations with or involvement in any organization or entity with any financial or non-financial interest in the subject matter or materials discussed in this manuscript.\u003c/p\u003e\n\u003cp\u003eThe authors have no financial or proprietary interests in any material discussed in this article.\u003c/p\u003e\n\u003cp\u003eThe research not involving any human participants and/or animals.\u003c/p\u003e"},{"header":"References","content":"\u003col\u003e\n\u003cli\u003eAl-Haddad K,\u0026quot;A modified wireless power transfer system for medical implants\u0026quot;, \u003cem\u003eEnergies\u003c/em\u003e, 2019, 12(10), 1-21, DOI https://doi.org/10.3390/en12101890\u003c/li\u003e\n\u003cli\u003eHaumann S, Bauernfeind G, Teschner MJ, Schierholz I, Bleichner MG, B\u0026uuml;chner A, Lenarz T, \u0026quot;Epidural recordings in cochlear implant users\u0026quot;, \u003cem\u003eJournal of neural engineering\u003c/em\u003e, 2019, 16(5), DOI https://doi.org/10.1088/1741-2552/ab1e80\u003c/li\u003e\n\u003cli\u003eZeng FG, Rebscher S, Harrison W, Sun X, Feng H, \u0026quot;Cochlear implants: system design, integration, and evaluation\u0026quot;, \u003cem\u003eIEEE reviews in biomedical engineering, \u003c/em\u003e2008, 1, 115-42, DOI 10.1109/RBME.2008.2008250\u003c/li\u003e\n\u003cli\u003eHeine, P. 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C., Choi, J, \u0026ldquo;Auditory brainstem response test results in normal hearing adolescents with subjective tinnitus\u0026rdquo;, International Journal of Pediatric Otorhinolaryngology, 2021, 146, 110775.\u003c/li\u003e\n\u003cli\u003eCourtois, G., Grimaldi, V., Lissek, H., Estoppey, P., Georganti, E, \u0026ldquo;Perception of auditory distance in normal-hearing and moderate-to-profound hearing-impaired listeners.\u0026rdquo; Trends in hearing, 2019, 23, 2331216519887615.\u003c/li\u003e\n\u003cli\u003eLahiani, M., Amor, N. B., Ghariani, H., Hamida, A. B, \u0026ldquo;Adjustable filtering structure design dedicated to a programmable hearing aid apparatus\u0026rdquo;, International Journal of Physical Sciences, 2006, 1(4), 201-211.\u003c/li\u003e\n\u003cli\u003eMost, T., Aviner, C, \u0026ldquo;Auditory, visual, and auditory\u0026ndash;visual perception of emotions by individuals with cochlear implants, hearing aids, and normal hearing\u0026rdquo;. Journal of Deaf Studies and Deaf Education, 2009, 14(4), 449-464.\u003c/li\u003e\n\u003cli\u003eBento, R. F., Kiesewetter, A., Ikari, L. S., Brito, R, \u0026ldquo;Bone-anchored hearing aid (BAHA): indications, functional results, and comparison with reconstructive surgery of the ear\u0026rdquo;, International archives of otorhinolaryngology, 2012, 16(03), 400-405.\u003c/li\u003e\n\u003cli\u003eSanders, M. E., Kant, E., Smit, A. L., Stegeman, I, \u0026ldquo;The effect of hearing aids on cognitive function: A systematic review\u0026rdquo;, Plos one, 2021, 16(12), e0261207.\u003c/li\u003e\n\u003cli\u003eH. Uluşan, S. Chamanian, B. İlik, A. Muhtaroğlu and H. K\u0026uuml;lah, \u0026quot;Fully Implantable Cochlear Implant Interface Electronics With 51.2\u0026micro;W Front-End Circuit,\u0026quot; in \u003cem\u003eIEEE Transactions on Very Large Scale Integration (VLSI) Systems\u003c/em\u003e, 2019, 27(7), 1504-1512, DOI 10.1109/TVLSI.2019.2898873\u003c/li\u003e\n\u003cli\u003eR. S. Pal, S. 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Dasgupta, \u0026quot;Recent trend of FinFET devices and its challenges: A review\u0026quot;, \u003cem\u003eConference on Emerging Devices and Smart Systems (ICEDSS)\u003c/em\u003e, 2017, 150-154. \u003cstrong\u003eDOI: \u003c/strong\u003e10.1109/ICEDSS.2017.8073675\u003c/li\u003e\n\u003cli\u003eGu Y, Aissa S, \u0026quot;RF-based energy harvesting in decode-and-forward relaying systems: Ergodic and outage capacities\u0026quot;, \u003cem\u003eIEEE Transactions on Wireless Communication\u003c/em\u003e, 2015, 14(11), 6425-434, DOI 10.1109/TWC.2015.2453418\u003c/li\u003e\n\u003cli\u003eHussong A, Rau TS, Ortmaier T, Heimann B, Lenarz T, Majdani O, \u0026quot;An automated insertion tool for cochlear implants: another step towards atraumatic cochlear implant surgery\u0026quot;, \u003cem\u003eInternational journal of computer assisted radiology and surgery\u003c/em\u003e, 2010, 5(2), 163-171, DOI 10.1007/s11548-009-0368-0\u003c/li\u003e\n\u003cli\u003eNagulapalli, R., Hayatleh, K., Barker, S., Zourob, S., Yassine, N., Raparthy, S., \u0026amp; Tammam, A. A novel high CMRR trans-impedance instrumentation amplifier for biomedical applications. Analog Integrated Circuits and Signal Processing,2019;98(2):233-241. DOI: https://doi.org/10.1007/s10470-018-1256-8\u003c/li\u003e\n\u003cli\u003eSrivastava, N., Shadab, A., \u0026amp; Shukla.G. Yokto (10-24V) Instrumentation Amplifier. IEEE Third International Conference on Computer and Communication Technology,2012;116-121. DOI: 10.1109/ICCCT.2012.31\u003c/li\u003e\n\u003c/ol\u003e"}],"fulltextSource":"","fullText":"","funders":[],"hasAdminPriorityOnWorkflow":false,"hasManuscriptDocX":true,"hasOptedInToPreprint":true,"hasPassedJournalQc":"","hasAnyPriority":false,"hideJournal":true,"highlight":"","institution":"","isAcceptedByJournal":false,"isAuthorSuppliedPdf":false,"isDeskRejected":"","isHiddenFromSearch":false,"isInQc":false,"isInWorkflow":false,"isPdf":false,"isPdfUpToDate":true,"isWithdrawnOrRetracted":false,"journal":{"display":true,"email":"[email protected]","identity":"researchsquare","isNatureJournal":false,"hasQc":true,"allowDirectSubmit":true,"externalIdentity":"","sideBox":"","snPcode":"","submissionUrl":"/submission","title":"Research Square","twitterHandle":"researchsquare","acdcEnabled":true,"dfaEnabled":false,"editorialSystem":"","reportingPortfolio":"","inReviewEnabled":false,"inReviewRevisionsEnabled":true},"keywords":"Cochlear Implant (CI), Fin Field Effect Transistor (FINFET), Prosthesis, Biopotential Amplifier, Noise Analysis","lastPublishedDoi":"10.21203/rs.3.rs-3412444/v1","lastPublishedDoiUrl":"https://doi.org/10.21203/rs.3.rs-3412444/v1","license":{"name":"CC BY 4.0","url":"https://creativecommons.org/licenses/by/4.0/"},"manuscriptAbstract":"Electrical stimulus inside the ear to provide an auditory response using advanced prosthesis for the deaf people is a challenging task. Recent advance like cochlear implant prosthesis with in-built electrode array configuration converts the acoustic energy to the electrical stimulus. In this article, we discuss about the invention of different hearing aid designed for hearing impairment patient. A biopotential amplifier is utilised in the internal unit of a cochlear implant to reduce noise from the external unit and radio frequency components. It is designed using the advanced Fin Field Effect Transistor (FINFET) 22 nm technology and compare the results with conventional CMOS technology. The operating voltage applied to entire design is of 0.45v, the measured noise is of 133.0563 nv/√Hz at 50Hz frequency.","manuscriptTitle":"A low noise biopotential amplifier intended for Cochlear Implant using FINFET 22nm technology","msid":"","msnumber":"","nonDraftVersions":[{"code":1,"date":"2025-02-11 09:49:57","doi":"10.21203/rs.3.rs-3412444/v1","editorialEvents":[{"type":"communityComments","content":0}],"status":"published","journal":{"display":true,"email":"[email protected]","identity":"researchsquare","isNatureJournal":false,"hasQc":true,"allowDirectSubmit":true,"externalIdentity":"","sideBox":"","snPcode":"","submissionUrl":"/submission","title":"Research Square","twitterHandle":"researchsquare","acdcEnabled":true,"dfaEnabled":false,"editorialSystem":"","reportingPortfolio":"","inReviewEnabled":false,"inReviewRevisionsEnabled":true}}],"origin":"","ownerIdentity":"fd275c67-7de4-4400-a488-230b1426c042","owner":[],"postedDate":"February 11th, 2025","published":true,"recentEditorialEvents":[],"rejectedJournal":[],"revision":"","amendment":"","status":"posted","subjectAreas":[],"tags":[],"updatedAt":"2025-03-18T16:04:35+00:00","versionOfRecord":[],"versionCreatedAt":"2025-02-11 09:49:57","video":"","vorDoi":"","vorDoiUrl":"","workflowStages":[]},"version":"v1","identity":"rs-3412444","journalConfig":"researchsquare"},"__N_SSP":true},"page":"/article/[identity]/[[...version]]","query":{"redirect":"/article/rs-3412444","identity":"rs-3412444","version":["v1"]},"buildId":"8U1c8b4HqxoKbykW_rLl7","isFallback":false,"isExperimentalCompile":false,"dynamicIds":[84888],"gssp":true,"scriptLoader":[]}